|Publication number||US7130690 B2|
|Application number||US 10/625,344|
|Publication date||Oct 31, 2006|
|Filing date||Jul 23, 2003|
|Priority date||Jul 23, 2003|
|Also published as||US20050021095, WO2005009529A2, WO2005009529A3|
|Publication number||10625344, 625344, US 7130690 B2, US 7130690B2, US-B2-7130690, US7130690 B2, US7130690B2|
|Inventors||John C. Rueter, Todd J. Sheldon|
|Original Assignee||Medtronic, Inc.|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (33), Referenced by (30), Classifications (11), Legal Events (3)|
|External Links: USPTO, USPTO Assignment, Espacenet|
This disclosure is related to the following co-pending U.S. patent application Ser. No. 10/260,984 filed Sep. 30, 2002, entitled METHOD AND APPARATUS FOR PERFORMING STIMULATION THRESHOLD SEARCHES by C. M. Manrodt et al., and co-pending U.S. patent application Ser. Nos. 10/004,164 filed Oct. 30, 2001, and Ser. No. 10/434,689 filed May 9, 2003, both for CAPTURE MANAGEMENT IMPROVEMENTS by John C. Rueter et al., which are not admitted as prior art with respect to the present disclosure by mention in this section.
This invention relates to implantable AV synchronous, dual chamber pacing systems, and particularly to improved determination of atrial capture during atrial pacing.
Atrial synchronized, dual chamber, pacing modes, particularly, the multi-programmable, VDD, VDDR, DDD and DDDR pacing modes, have been widely adopted in implantable dual chamber pacemakers for providing atrial and ventricular or AV synchronized pacing on demand. Such dual chamber pacing modes have also been incorporated into implantable cardioverter/defibrillators (ICDs) and into right and left heart pacing systems providing synchronized right and left heart pacing for enhancing left ventricular cardiac output as described in commonly assigned U.S. Pat. No. 5,902,324.
Such pacing systems are embodied in an implantable pulse generator (IPG) adapted to be subcutaneously implanted and at least atrial and ventricular pacing or cardioversion/defibrillation leads that are coupled to the IPG. The atrial and ventricular leads each incorporate one or more lead conductor that extends through the lead body to an exposed pace/sense electrode or cardioversion/defibrillation electrode disposed in operative relation to a heart chamber.
The pacing operating system comprises atrial and ventricular sense amplifiers and atrial and ventricular pace pulse generators. The atrial sense amplifier is coupled to active and indifferent atrial pace/sense electrodes to detect electrical signals of the heart associated with atrial depolarizations (P-waves) and to generate an atrial sense event (A-EVENT) signal when detection criteria are met. The ventricular sense amplifier is coupled to active and indifferent ventricular pace/sense electrodes to detect electrical signals of the heart associated with ventricular depolarizations (R-waves) and to generate a ventricular sense event (V-EVENT) signal when detection criteria are met. The atrial pace pulse generator delivers a negative-going or cathodal voltage atrial pacing (A-PACE) pulse through a pacing path comprising the active and indifferent atrial pace/sense electrode. The ventricular pace pulse generator delivers a negative-going or cathodal voltage atrial pacing (V-PACE) pulse through a pacing path comprising the active and indifferent ventricular pace/sense electrode.
The pacing operating system times out various intervals from each A-EVENT, V-EVENT, A-PACE, and V-PACE to maintain synchronous depolarizations of the atria and ventricles. Such AV synchronous pacemakers that perform this function have the capability of tracking the patient's natural sinus rhythm and preserving the hemodynamic contribution of the atrial contraction over a wide range of heart rates. Maintenance of AV mechanical synchrony is of great importance as set forth in greater detail in commonly assigned U.S. Pat. No. 5,626,623.
Each of the A-PACE and V-PACE pulse energies is set at a programmable energy level, involving both pulse width (duration) and amplitude (strength), so as to provide sufficient energy to cause the heart chamber to depolarize and contract. The minimum pacing pulse energy which is required to capture and thus evoke a muscular depolarization within the heart is referred to as the “stimulation threshold”, and generally varies in accordance with the well known strength-duration curves, wherein the amplitude of a stimulation threshold current pulse and its duration are inversely proportional. When a delivered pacing pulse is successful in so stimulating the heart into contraction, it is said to have “captured” the heart, whereas failure to stimulate the heart is described as “loss of capture” (LOC).
In order to maximize the useful life of dual chamber pacing IPGs, it is desirable that the A-PACE pulse energy and the V-PACE pulse energy be programmed to the minimal energies required to capture the atria and ventricles, respectively. As is well known, the stimulation threshold for a patient, in both the atrium and the ventricle, can fluctuate both short term and long term following implantation. The A-PACE and V-PACE pulse energies are therefore typically programmed by the physician at implantation employing an external programmer to exceed the stimulation threshold by a “safety margin” to avoid atrial loss of capture (ALOC) and ventricular loss of capture (VLOC).
As described in commonly assigned U.S. Pat. No. 5,324,310, the post-operative determination of the stimulation thresholds by the physician typically requires the patient to be connected to surface ECG equipment while a threshold routine is conducted using the pacemaker programmer. The pacemaker programmer successively reprograms the pulse width and/or amplitude on a temporary basis to ascertain the points at which capture is lost. The A-PACE and/or V-PACE pulses are observed on a display or paper tracing as spikes, and capture or LOC is observed by the presence or absence of the “evoked response” wave shape (a P-wave or an R-wave) that follows each spike. At LOC, the programmed pacing pulse may be immediately restored so that the patient does not experience syncope. A strength-duration curve may be plotted from the resulting threshold data. The resulting threshold data may then be used to permanently reprogram the pulse energy. Naturally, such periodic patient studies are time-consuming and expensive to conduct. Moreover, they do not provide an indication of stimulation threshold fluctuation over the course of a patient's day and levels of activity.
Therefore, systems and methods have been proposed to be incorporated or have been incorporated into the IPG operating system to periodically, automatically conduct stimulation threshold tests, and to readjust the pacing pulse energy in relation to any newly determined stimulation threshold. See, for example, U.S. Pat. No. 3,920,024, where the pacing pulse energy is initially set at a high enough energy to ensure capture, and then is reduced by successive increments until LOC is detected and a back-up pacing pulse is delivered. The evoked response characteristic of capture is intended to be sensed across a particular pace/sense electrode pair, and LOC is inferred if the evoked response is not detected within a short time window following delivery of the pacing pulse.
However, sensing of the evoked response is rendered difficult for a variety of reasons. The A-PACE and V-PACE pulses are produced by the exponential discharge of respective atrial and ventricular output capacitors through the impedance loads in the atrial and ventricular pacing paths that each include a coupling capacitor, the active and indifferent pace/sense electrodes, and the patient's heart tissue between the pace/sense electrodes. It is conventional to suppress or blank both of the atrial and ventricular sense amplifiers during A-PACE and V-PACE pulses for blanking periods to avoid overloading the sense amplifier, to allow a fast recharge function to be completed, and to prevent sensing of artifacts resulting in false declarations of A-EVENTs or V-EVENTs.
In addition, a number of sense amplifier refractory periods are timed out on atrial and ventricular sense event signals and generation of A-PACE and V-PACE pulses, whereby “refractory” A-EVENT and V-EVENTs during such refractory periods are selectively ignored or employed in a variety of ways to reset or extend time periods being timed out. The durations of the blanking and refractory periods therefore render it difficult to reliably detect an evoked response, if any, across the same pace/sense electrode pair that the A-PACE or V-PACE pulse is delivered across.
As a result of these considerations, a great deal of effort has been expended over many years to develop IPGs having the capability of automatically testing the stimulation threshold, i.e. providing an “auto-capture” detection function, and resetting the pacing pulse energy to exceed the threshold by the safety margin without the need for clinical or patient intervention.
Commonly assigned U.S. Pat. Nos. 6,134,473 and 6,144,881 describe the Capture Management algorithm implemented, for example, in the Medtronic® Kappa® 700 pacemaker IPGs. The polarity of the positive or negative change in voltage with respect to time (or dv/dt) of the waveform incident on the pace/sense electrodes is monitored during a short period of time immediately following a paced event. In one embodiment, sensing of the evoked response is based upon a relationship between a maximum magnitude of a derivative of a sensed signal and a predetermined threshold reference value. The evoked response is declared when the maximum amplitude of the derivative of the sensed signal equals or exceeds the threshold reference value.
The Capture Management algorithm is periodically run, e.g., once a day at a prescribed time to perform a pacing threshold search (PTS) wherein the pacing pulse amplitudes and pulse widths of the pacing pulses delivered in each pacing channel are incrementally adjusted within a predetermined range to determine the pacing threshold, and the threshold data is stored for analysis of long term trends. When an “Adaptive” mode of the Capture Management algorithm is programmed the Capture Management algorithm automatically adjusts the pacing pulse amplitude and/or pulse width setting to ensure capture at minimum pacing energy while maintaining the programmed safety margin(s).
A wide variety of other approaches have been taken as reflected by the extensive listing of earlier patents described in the above-referenced '310 patent and in commonly assigned U.S. Pat. Nos. 5,320,643, 5,324,310, 5,331,966, 5,601,615, 5,683,431, 5,861,012, 5,861,013, and 6,231,607, for example, and in further U.S. Pat. Nos. 4,686,988, 5,165,404, 5,165,405, 5,172,690, 5,222,493, 5,285,780, 5,564,430, and 5,683,426, for example.
The '310 patent, for example, discloses employing additional capture detection sense amplifiers and sense electrode pairs to detect the evoked response within an anticipated time following delivery of an A-PACE or V-PACE pulse. In other approaches, as exemplified by the above referenced '643 patent, one or more physiologic sensors that show a response to the mechanical action of the heart, e.g. a piezoelectric or impedance sensor, or that show changes in physical properties of the blood when the heart is captured, e.g. blood pH, temperature, impedance or blood pressure sensors on the pacing lead have also been suggested. In virtually all of these approaches, it is necessary to rely on additional components and circuitry that consume more energy and add to the bulk and cost of the system and raise reliability issues.
In one atrial auto-capture approach disclosed in U.S. Pat. No. 5,476,486, for example, the amplitudes of a series of A-PACE pulses are progressively decremented, and the presence or absence of a V-EVENT within an AV delay is noted. The absence of a V-EVENT indicates ALOC.
In one embodiment of the above-referenced '615 and '012 patents particularly for use with patients having intact and regular A-V conduction and with or without an intrinsic atrial sinus rhythm, A-PACE pulses are delivered at a test escape interval (that is shorter than any intrinsic atrial interval) and a paced AV (PAV) delay is timed out. An ALOC is declared in the absence of a detected V-EVENT in the latter portion of the test PAV delay following the delivery of the A-PACE test pulse. In the ventricular threshold test regimen, a V-PACE test pulse is delivered after a shortened test PAV delay timed from the preceding A-PACE pulse. A VLOC is declared by the detection of a V-EVENT in the ventricular refractory period of the delivered V-PACE pulse.
These atrial capture detection methods depend upon normal AV conduction, which is not present in many instances where the patient is pacemaker dependent in the ventricles. Therefore, these methods cannot be used if the patient has a high degree of AV block since an A-PACE triggered atrial depolarization is not conducted reliably to the ventricles to trigger a ventricular depolarization sensed as a V-EVENT.
In a second embodiment of the '615 and '012 patents, for use in the atrium or ventricle in patients having intrinsic sinus rhythm, each test A-PACE or V-PACE pulse is delivered at a test escape interval set as a fraction, e.g., about 50%–75% of the average intrinsic escape interval timed from a preceding A-EVENT or V-EVENT, respectively. A sense test window set to be somewhat longer than the test escape interval is timed out from delivery of the test A-PACE or V-PACE pulse. ALOC or VLOC is declared if an A-EVENT or V-EVENT, respectively, is detected within the sense test window. A-CAPTURE or V-CAPTURE is declared if an A-EVENT or V-EVENT, respectively, is detected after time-out of the sense test window. The energy of the test A-PACE pulse is successively incremented or decremented until an A-EVENT is detected within the sense test window, which signifies ALOC at the test energy of the previously delivered A-PACE test pulse. Preferably, in this embodiment, the test energy in pulse width and amplitude of the A-PACE or V-PACE test pulses is increased until A-CAPTURE or V-CAPTURE is declared so that the patient's normal rhythm is not disturbed frequently during the test.
These atrial and ventricular auto-capture methods depend upon the presence of normal sinus rhythm in the atrium and ventricles, respectively, which is not present in many instances where the patient is pacemaker dependent in one or both of the atria and the ventricles. In such a case, the sense test window cannot be determined since intrinsic A-EVENTs and V-EVENTs cannot be reliably detected.
Further auto-capture methods disclosed in U.S. Pat. Nos. 5,476,487, 5,674,254, and 6,216,037, rely upon the observation that the QT interval of the PQRST waveform varies in duration as a function of capture or LOC of the ventricles following a V-PACE or the atria following an A-PACE conducted to the ventricles. The commonly assigned '037 patent discloses an implantable DDD pacemaker incorporating a method for continually determining whether a delivered A-PACE pulse has resulted in capture of the atrium. A V-PACE is delivered after the time-out of a PAV delay, and the following QT interval is determined. An atrial depolarization that spontaneously occurs during the time-out of the PAV can affect the QT interval. The QT interval is measured on a cycle-by-cycle basis, stored, and employed in making a determination of change in QT interval, i.e., )QT=*QT−QTPREV*. The )QT variable is compared to a lower limit, e.g., 2 ms, and a higher limit, e.g., 10 ms, and when )QT is within this range there is a determination of ALOC.
Detecting the QT interval following delivery of a V-PACE using the ventricular sense amplifier is itself difficult given the ventricular blanking and refractory intervals. Moreover, this approach presumes that the atria have an intrinsic depolarization rate that is overdriven at a faster atrial pacing rate. It also assumes that there is intact AV conduction, but that the ventricles are also paced. Typically, atrial and ventricular synchronized pacing is necessary during AV block and when the intrinsic atrial heart rate is lower than is desirable to provide sufficient cardiac output to meet the patient's needs.
What is needed in the art of determining ALOC is a capability of reliably detecting when a delivered A-PACE pulse has evoked an atrial depolarization without requiring special tests or additional components or circuitry that consume energy and add to the bulk and cost of the system. Specifically, there is a substantial need in a pacing system for an atrial capture detection method and system that function simply and reliably when the patient is pacemaker dependent in the atria or in both the atria and the ventricles.
In accordance with the present invention, simple and effective systems and methods for determining A-CAPTURE and ALOC are provided in AV synchronous, dual chamber, pacing systems or any atrial based pacing system.
In the atrial capture management (ACM) algorithms of the present invention, the A-PACE pulse energy, defined by the pulse width and pulse amplitude, is sufficient to reliably capture the atrium without being wasteful of battery energy is periodically determined. The ACM algorithms allow a slow intrinsic atrial heart rate that is suppressed by delivered A-PACE pulses resulting in A-CAPTURE and that occurs when delivered test A-PACE pulses result in ALOC to be detected. ALOC is declared if an A-EVENT of the slow intrinsic atrial heart rate is detected either during an ACM test window timed from the delivered test A-PACE pulse or during delivery of a sequence of test A-PACE pulses delivered within or defining the ACM test window. In particular embodiments, ALOC declaration is made when the slow intrinsic atrial heart rate is detected within the ACM test window in repeated delivery of the test A-PACE pulses and time-out of the ACM test window.
In certain embodiments, a series of test A-PACE pulses are delivered within the ACM test window, and ALOC is declared if a refractory or non-refractory A-EVENT occurs during the delivery of the test A-PACE pulses. In these embodiments, ventricular pacing and sensing can be provided during delivery of the test A-PACE pulses in a dual chamber pacing mode, e.g., a DDD pacing mode. The occurrence of a refractory or non-refractory A-EVENT signifies that the series of test A-PACE pulses have not resulted in A-CAPTURE, allowing the atria to depolarize at the slow intrinsic atrial heart rate, unless the A-EVENT is deemed to represent far field sensing of a ventricular depolarization or a retrograde conduction of a ventricular depolarization.
In a further embodiment, atrial and ventricular pacing is suppressed over the ACM test window by prolonging the A-A pacing escape interval from the last delivered test A-PACE pulse to time-out the ACM test window. Any A-EVENT detected during time out of the prolonged escape interval signifies that the test A-PACE pulse did not result in A-CAPTURE, allowing the atria to depolarize at the slow intrinsic atrial heart rate, unless the A-EVENT is deemed to represent far field sensing of a ventricular depolarization or a retrograde conduction of a ventricular depolarization.
The sensed refractory or non-refractory A-EVENT is deemed to represent far field sensing of a ventricular depolarization V-EVENT or a retrograde conduction of a ventricular depolarization if the A-EVENT closely follows (within a defined window) a V-EVENT or a delivered V-PACE. Preferably, an abort count is incremented in that case, and the ACM algorithm is aborted if repeated sensing of retrograde conducted V-EVENTs or far field sensing of V-EVENTs occurs.
Advantageously, it is fairly simple to determine that a patient has a slow atrial rhythm from ECG or EGM tracings and during testing at implantation and at follow-ups. Further, the present method may work in patients in whom the methods in the prior art may fail because, for example, the patient did not have the stable AV conduction needed for one method, or because the patient was paced at too high a rate for another method to be effectively used.
The ACM algorithms of the present invention can be programmed ON or OFF by the physician responsible for the patient.
This summary of the invention has been presented here simply to point out some of the ways that the invention overcomes difficulties presented in the prior art and to distinguish the invention from the prior art and is not intended to operate in any manner as a limitation on the interpretation of claims that are presented initially in the patent application and that are ultimately granted.
These and other advantages and features of the present invention will be more readily understood from the following detailed description of the preferred embodiments thereof, when considered in conjunction with the drawings, in which like reference numerals indicate identical structures throughout the several views, and wherein:
In the following detailed description, references are made to illustrative embodiments of methods and apparatus for carrying out the invention. It is understood that other embodiments can be utilized without departing from the scope of the invention.
The present invention can be implemented in a dual chamber pacing system that is incorporated into a dual chamber pacemaker, a multi-chamber pacemaker providing right and left atrial and ventricular pacing, or an ICD or other IMD incorporating such pacing systems. The following description of a dual chamber pacemaker is thus intended to encompass all of the various types of dual chamber pacing systems in which the present invention can be implemented.
Such a dual chamber IPG 100 and unipolar or bipolar atrial and ventricular leads 114 and 116 (bipolar leads are depicted), in which the present invention may be implemented is depicted in
The dual chamber pacemaker IPG 100 senses and paces in the atrial and ventricular chambers, and pacing is either triggered and inhibited depending upon sensing of intrinsic, non-refractory atrial and ventricular depolarizations during the sequentially timed A-A escape interval and AV delay, respectively, as is well known in the art, in accordance with the steps set forth in the flow chart of
The IPG 100 is provided with a hermetically sealed enclosure or can 118, typically fabricated of biocompatible metal such as titanium, enclosing the dual chamber IPG circuit 300 depicted in
An electrically exposed area of the can 118 can also function as an IND_CAN electrode 140 that is electrically connected to one input of a far field sense amplifier to facilitate sensing of the atrial and/or ventricular EGM for storage and analysis in various ways known in the art. It is also possible to program an indifferent electrode selection to use the IPG 100 IND_CAN electrode 140 is as an indifferent pace/sense electrode for unipolar atrial and/or ventricular pacing.
The bipolar atrial pacing lead 116 extends between its proximal connector coupled to IPG 100 and distal atrial pace/sense electrodes 120 and 122 located in the right atrium 12 of heart 10 to enable sensing of P-waves and delivery of atrial pacing pulses to the right atria. A-PACE pulses may be delivered between atrial pace/sense electrodes 120 and 122 in a bipolar pacing mode or between atrial pace/sense electrode 122 and the IND_CAN electrode 140 of the IPG 100 in a unipolar pacing mode. Sensing of P-waves by the atrial sense amplifier may occur between atrial pace/sense electrodes 120 and 122 in a bipolar sensing mode or between either of atrial pace/sense electrode 120 and 122 and the IND_CAN electrode 140 of the IPG 100 in a unipolar atrial sensing mode.
Similarly, the bipolar ventricular pacing lead 114 extends between its proximal connector coupled to IPG 100 and distal ventricular pace/sense electrodes 128 and 130 located in the right ventricle 16 of heart 10 to both sense R-waves and to deliver ventricular pacing pulses to the ventricles. V-PACE pulses may be delivered between ventricular pace/sense electrodes 128 and 130 in a bipolar pacing mode or between ventricular pace/sense electrode 130 and the IND_CAN electrode 140 of the IPG 100 in a unipolar pacing mode. Sensing of R-waves by the ventricular sense amplifier occurs between ventricular pace/sense electrodes 128 and 130 in a bipolar sensing mode or between either of ventricular pace/sense electrode 128 and 130 and the IND_CAN electrode 140 of the IPG 100 in a unipolar ventricular sensing mode.
The IPG circuit 300 within IPG 100 and the bipolar atrial and ventricular leads 114 and 116 are depicted in
The depicted counters and timers within digital controller/timer circuit 330 include ABP and VBP timers 366, intrinsic interval timers 368 for timing average intrinsic A-A and V-V intervals from A-EVENTs and V-EVENTs, escape interval timers 370 for timing A-A, V-A, and/or V-V pacing escape intervals, an AV delay timer 372 for timing the SAV delay from a preceding A-EVENT or PAV delay from a preceding A-TRIG, refractory period timers 374 for timing ARP, PVARP and VRP times, and an ACM controller 376 for controlling performance of the ACM functions of the present invention. Digital controller/timer circuit 330 starts and times out these intervals and time periods that are calculated by microcomputer circuit 302 for controlling the above-described operations of the atrial and ventricular sense amplifiers in sense amplifiers circuit 360 and the atrial and ventricular pace pulse generators in output amplifier circuit 340.
Preferably, the IPG 100 or one of the leads 114 or 116 includes one or more physiologic sensor that develops a physiologic signal that relates to the need for cardiac output. The use of physiologic sensors to provide variation of pacing rate in response to sensed physiologic parameters, such as physical activity, oxygen saturation, blood pressure and respiration, has become commonplace. The rate-adaptive VDDR, DDIR, and DDDR pacing modes function in the above-described manner but additionally provide rate modulation of a pacing escape interval between a programmable lower rate and an upper rate limit (URL) as a function of a physiologic signal or rate control parameter (RCP) related to the need for cardiac output developed by a physiologic sensor. At times when the intrinsic atrial rate is inappropriately high or low, a variety of “mode switching” schemes for effecting switching between tracking modes and non-tracking modes (and a variety of transitional modes) based on the relationship between the atrial rate and the sensor derived pacing rate have been proposed as exemplified by commonly assigned U.S. Pat. No. 5,144,949.
Commonly assigned U.S. Pat. Nos. 4,428,378 and 4,890,617 disclose activity sensors that are employed to vary the pacing escape interval in single and dual chamber pacemaker IPGs in response to sensed physical activity. Such an activity sensor 316 is coupled to the inside surface of the IPG hermetically sealed enclosure 118 and may take the form of a piezoelectric crystal transducer as is well known in the art. The activity sensor 316 generates an output signal in response to certain patient activities, e.g. ambulating, that is processed and used as the RCP. If the IPG operating mode is programmed to a rate responsive mode, the patient's activity level developed in the patient activity circuit (PAS) 322 is monitored, and a sensor derived V-A, A-A or V-V escape interval is derived proportionally thereto. A timed interrupt, e.g., every two seconds, may be provided in order to allow the microprocessor 304 to analyze the output of the activity circuit PAS 322 and update the basic V-A (or A-A or V-V) escape interval employed to govern the pacing cycle and to adjust other time intervals as described below.
The bipolar leads 114 and 116 are illustrated schematically with their associated pace/sense electrode sets 120, 122 and 128, 130, respectively, as coupled directly to the atrial and ventricular pacing pulse output circuit 340 and sense amplifiers circuit 360 of pacing circuit 320. The atrial and ventricular pacing pulse output circuit 340 and sense amplifiers circuit 360 contain pulse generators and sense amplifiers corresponding to any of those presently employed in commercially marketed cardiac pacemakers for atrial and ventricular pacing and sensing.
In order to trigger generation of a V-PACE pulse, digital controller/timer circuit 330 generates a V-TRIG signal at the end of a PAV or SAV delay provided by AV delay timer 372. Similarly, in order to trigger an atrial pacing or A-PACE pulse, digital controller/timer circuit 330 generates an A-TRIG signal at the termination of the A-A escape interval timed out by escape interval timers 370. The pulse width (PW) and pulse amplitude (PA) of the A-PACE pulse and V-PACE pulse width is defined by PA and PW signals that are either the prevailing programmed PA and PW or are periodically determined in an ACM algorithm. The A-PACE and V-PACE pulses are produced by the exponential discharge of respective atrial and ventricular output capacitors through the impedance loads in the atrial and ventricular pacing paths that each include a coupling capacitor, the active and indifferent pace/sense electrodes, and the patient's heart tissue between the pace/sense electrodes.
Sense amplifiers circuit 360 includes atrial and ventricular sense amplifiers of the types disclosed for example, in the above-referenced '013 patent. Sense amplifiers circuit 360 also comprises a far field sense amplifier coupled with the IND_CAN electrode 140 and one of the ventricular pace/sense electrodes 128 or 130 selected by a SELECT signal so that a far field atrial and/or ventricular EGM can be sensed along a bipolar or far-field sense vector.
Sensitivity settings of the atrial and ventricular sense amplifiers and the EGM sense amplifier in sense amplifiers circuit 360 can be programmed by the physician to reliably sense true P-waves, R-waves and premature ventricular contractions (PVCs) during a patient work-up at implantation or during a patient follow-up telemetry session so that true A-EVENT and V-EVENT signals are generated. Digital controller/timer circuit 330 controls the sensitivity settings of the atrial and ventricular sense amplifiers in sense amplifiers circuit 360 by means of sensitivity control 350.
It is conventional to suppress or blank both of the atrial and ventricular sense amplifiers during A-PACE and V-PACE pulses for blanking periods to avoid overloading the sense amplifier. Moreover, the sense amplifiers may abruptly sense a different potential than was present at the time of initial blanking when the blanking period expires and the sense amplifier is reconnected due to the after-potentials and electrode polarization as well as the recharge function. This can produce unwanted oversensing of artifacts resulting in false declarations of A-EVENTs or V-EVENTs. Therefore, the blanking periods in pacemaker IPGs sold by the assignee of this application are nominally set at 30 ms after delivery of an A-PACE or V-PACE, but the blanking periods may be programmed as long as 45 ms in difficult sensing scenarios. There may be additional digital blanking of the sense amplifiers to avoid sensing of evoked response or other pacing artifacts, e.g., for 150 ms to 400 ms after paced events in ICDs.
Accordingly, ABP and VBP timers in block 366 of digital controller/timer circuit 330 time out an atrial blanking periods (ABP) including a post A-PACE, atrial blanking period (PAABP or PAAB) and a post V-PACE, atrial blanking period (PVABP or PVAB) or as a ventricular blanking periods (VBP) including a post A-PACE, ventricular blanking period (PAVBP or PAVB), and a post V-PACE, ventricular blanking period (PVVBP or PVB). Thus, the appropriate atrial blanking (A-BLANK) signal is applied to the atrial sense amplifier for the prevailing ABP, and a ventricular blanking (V-BLANK) signal is applied to the ventricular sense amplifier for the prevailing VBP. In the absence of an A-BLANK signal, atrial depolarizations or P-waves that are detected by the atrial sense amplifier result in an A-EVENT that is communicated to the digital controller/timer circuit 330. Similarly, in the absence of a V-BLANK signal, ventricular depolarizations or R-waves that are detected by the ventricular sense amplifier result in a V-EVENT that is communicated to the digital controller/timer circuit 330.
As noted above, after-potentials on the ventricular pace/sense electrodes at time-out of the PAVBP can erroneously be detected and result in declaration of a V-EVENT by the ventricular sense amplifier. The pacing system will not provide appropriate ventricular pacing to a patient's heart having AV block if electrical noise or other signals are mistakenly sensed by the ventricular sense amplifier as V-EVENTs during time-out of the AV delay. The questionable nature and consequences of mistakenly detecting V-EVENTs has led to the adoption of the practice of delivering a ventricular safety pace (VSP) pulse at a fixed time, typically 110 ms, following delivery of an A-PACE. In other words, a VSP pulse is delivered to the ventricular pace/sense electrodes if a V-EVENT is declared between the time-out of the PAVBP and a 110 ms VSP window following delivery of an A-PACE pulse. This 110 ms VSP window is often denoted the cross talk window. The 110 ms VSP window length is shorter than the normal AV conduction time in humans, so any V-EVENT declared within the VSP window is unlikely to be due to true AV conduction. The delivered VSP pulse captures the ventricles if the V-EVENT was due to cross talk, that is, sensing of the residual A-PACE energy after-potentials. The delivered VSP pulse will not capture the ventricles if the V-EVENT reflects a PVC, because the ventricles will be refractory at that time. Thus, faced with this uncertainty, a VSP pulse is delivered at time-out of the VSP window or delay so as to ensure that the ventricles are truly contracting at a safe time after delivery of the A-PACE pulse. The VSP window is timed out by a VSP timer in block 366 of digital controller/timer circuit 330.
In addition, a number of sense amplifier refractory periods are timed out on A-EVENT and V-EVENT signals and generation of A-PACE and V-PACE pulses, whereby “refractory” A-EVENT and V-EVENTs during such refractory periods are selectively ignored or employed in a variety of ways to reset or extend time periods being timed out. The refractory period timers 374 time out atrial and ventricular refractory periods (ARP and VRP) commenced upon an A-EVENT or V-EVENT or generation of an A-PACE or V-PACE pulse, respectively. The ARP is typically only employed by itself during atrial demand pacing in the AAI pacing mode. In dual chamber pacing modes, the ARP commenced by the A-EVENT or A-PACE pulse extends through the SAV delay or the PAV delay until a certain time following a V-EVENT terminating the SAV or PAV delay or generation of a V-PACE pulse at the expiration of the SAV or PAV delay. This post-ventricular atrial refractory period (PVARP) is commenced by a V-PACE pulse or V-EVENT based on the understanding that A-EVENTs sensed during its time-out generally reflect a retrograde conduction of the evoked or spontaneous ventricular depolarization wave and therefore are not employed to reset an escape interval and commence an SAV delay. The duration of PVARP may be fixed or vary as a function of sensed atrial rate or pacemaker defined pacing rate, with the result that in many cases relatively long PVARPs are in effect at lower rates. A total ARP (TARP) is defined as the entire duration of the ARP and the PVARP.
An A-EVENT is characterized as a refractory A-EVENT (AR-EVENT in the following) if it occurs during time-out of an ARP or a PVARP or a non-refractory A-EVENT if it occurs after time-out of these atrial refractory periods. Similarly, a V-EVENT is characterized as a refractory V-EVENT (VR-EVENT in the following) if it occurs during time-out of a VRP or a non-refractory V-EVENT if it occurs after time-out of the ventricular refractory period. AR-EVENTs and VR-EVENTs are typically ignored for purposes of resetting timed out AV delays and A-A escape intervals, although diagnostic data may be accumulated related to their occurrences. However, in accordance with the ACM algorithms of the present invention an AR-EVENT detected during the ACM test window is treated the same as an A-EVENT to signify ALOC as described further below.
Microcomputer 202 contains a microprocessor 304 and associated system clock 308 and on-processor RAM and ROM chips 310 and 312, respectively. In addition, microcomputer circuit 302 includes a separate RAM/ROM chip 314 to provide firmware and additional RAM memory capacity. Microprocessor 304 is interrupt driven, operating in a reduced power consumption mode normally, and awakened in response to defined interrupt events, which may include the A-TRIG, V-TRIG, A-EVENT and V-EVENTs.
Microcomputer 302 controls the operational functions of digital controller/timer 324, specifying which timing intervals are employed in a programmed pacing mode via data and control bus 306. The specific values of the intervals timed by the digital controller/timer circuit 330 are controlled by the microcomputer circuit 302 by means of data and control bus 306 from programmed-in parameter values. The microcomputer 302 also calculates the RCP derived or intrinsic atrial rate derived V-V, A-A or A-A escape interval, the variable AV delay, and the variable ARP, PVARP and VRP. Typically, the AV delay in modern VDD, VDDR, DDD and DDDR pacemakers is either fixed or varies with the prevailing intrinsic atrial rate, measured as an A-A interval, and/or varies as a function of a physiologic sensor derived pacing rate.
Digital controller/timer circuit 330 also interfaces with other circuits of the input output circuit 320 or other components of IPG circuit 300. Crystal oscillator circuit 338 provides the basic timing clock and battery 318 provides power for the pacing circuit 320 and the microcomputer circuit 302. Power-on-reset circuit 336 responds to initial connection of the circuit to the battery 318 for defining an initial operating condition and similarly, resets the operative state of the IPG circuit 300 in response to detection of a low battery condition. Reference mode circuit 326 generates stable voltage reference and currents for the analog circuits within the pacing circuit 320. ADC (analog to digital converter) and multiplexer circuit 328 digitizes analog signals and voltage to provide real time telemetry of cardiac signals from sense amplifiers 360, for uplink transmission via RF transmitter and receiver circuit 332. Voltage reference and bias circuit 326, ADC and multiplexer 328, power-on-reset circuit 336 and crystal oscillator circuit 338 may correspond to any of those presently used in current marketed implantable cardiac pacemakers.
Data transmission to and from an external programmer (not shown) during a telemetry session is accomplished by means of the telemetry antenna 334 and an associated RF transmitter and receiver 332, which serves both to demodulate received downlink telemetry and to transmit uplink telemetry. Uplink telemetry capabilities will typically include the ability to transmit stored digital information, e.g. operating modes and parameters, EGM histograms, and other events, as well as real time EGMs of atrial and/or ventricular electrical activity and Marker Channel pulses indicating the occurrence of sensed and paced depolarizations in the atrium and ventricle, as are well known in the pacing art.
Reed switch 317 when closed by application of a magnetic field may be employed to enable programming of the pacemaker and also may be employed to convert the pacemaker temporarily to an asynchronous pacing mode such as DOO or VOO. Operation in the asynchronous mode may continue as long as the magnetic field is present, may continue until overridden by the programmer or may continue for a pre-set time period.
The illustrated IPG circuit 300 of
For convenience, the pacing cycle is assumed to begin at step S100 starting from a non-refractory A-EVENT sensed in step S118. Timing of the prevailing SAV delay set in step S122 and the post A-EVENT time periods described above are commenced in step S100. The operating system awaits either time out of the SAV delay in step S102 or a non-refractory V-EVENT in step S104. A V-PACE is delivered in step S108 upon time-out of the SAV delay without a V-EVENT declared in step S104. The SAV delay is terminated without delivery of a V-PACE pulse if a V-EVENT is declared in step S104.
In either case, the A-A escape interval time-out is commenced in step S108, and time-out of the post ventricular time periods including the VRP, PVARP, PAVBP and PVVBP are commenced in step S110. The algorithm awaits expiration of the A-A escape interval at step S112, and it is possible that a refractory or non-refractory A-EVENT or V-EVENT can occur during the A-A escape interval time-out.
The A-A escape interval is terminated if a non-refractory A-EVENT is sensed in step S118 during time-out the A-A escape interval. The AV delay is set to the SAV delay in step S122, and the SAV delay and associated post atrial sense ARP is timed out in step S100. Optionally, the non-refractory A-EVENT also causes the A-A escape interval to be measured by intrinsic interval timer 368 and employed to derive or update an intrinsic atrial rate that is saved in RAM. The A-A escape interval, the SAV and PAV delays, the PVARP, and the pacing escape interval for the next cardiac cycle can then be recalculated in dependence upon either the updated average A-A interval or upon the RCP in a manner well known in the art. For convenience, the A-A escape interval that is determined and timed out over the period between successive performances of the ACM algorithm is referred to as the “prevailing A-A escape interval” herein.
If a non-refractory V-EVENT is declared sensed by the ventricular sense amplifier at step S120 during time out of the A-A escape interval in the absence of detection of a preceding A-EVENT, then the declared V-EVENT is characterized as a PVC. The time-out of the prevailing A-A escape interval is halted in response to the PVC, and time-out of a V-A escape interval in step S106 and the post-ventricular time periods in step S110 are commenced. Certain algorithms, e.g., those disclosed in commonly assigned U.S. Pat. No. 6,311,088, have been devised to deal with such PVCs occurring during the A-A escape interval that could be practiced along with but are not necessary to the practice of the present invention.
An A-TRIG signal is generated leading to delivery of an A-PACE pulse in step S114 at the time-out of the A-A escape interval if the A-A escape interval times out without sensing any such intervening non-refractory A-EVENT or V-EVENT. In this case, the next succeeding AV delay is defined to be equal to PAV at step S116, and the PAV and post A-PACE time periods described above are timed out in step S100. The operating system awaits either time out of the PAV delay in step S102 or a non-refractory V-EVENT in step S104.
Various embodiments of the ACM algorithm of the present invention are set forth in
The various embodiments of the ACM algorithms of the present invention typically function when the patient is paced in the atrium. The patient's heart could, for example, be chronoptropically incompetent, such that the prevailing A-A escape interval is being set as a function of the output of the PAS circuit 322 or when the patient's intrinsic atrial heart rate as evidenced by the interval or cycle length between successive A-EVENTS falls below the pacing lower rate, which is typically programmed at about 1000 ms (60 bpm). Such patients may have an underlying sinus atrial rate of 25–60 bpm, for example, that is suppressed by the delivered A-PACE pulses as long as A-CAPTURE results. Moreover, the ACM algorithms of the present invention function when the patient is in AV block. As noted above, it is fairly simple to determine that the atria do or do not have an underlying slow intrinsic rate. Furthermore, the ACM algorithms of the present invention function when the patient's rhythm and rate would otherwise appear to be suited to algorithms of other methods, such as those that require stable AV conduction or that require stable intrinsic atrial sensing intervals, since the patient may have, for example, stable atrial sensing but at a rate may be too high for alternative methods, or AV conduction but at intervals too variable for alternative methods.
Thus, in step S204, the alternative methods, e.g., the capture management methods described in the above-referenced patent application Ser. Nos. 10/004,164 and 10/434,689, are performed. Normal pacing is resumed in step S200 of it is possible to successfully use those alternative algorithms of step S204 to determine ALOC and set the new prevailing A-PACE energy as determined in step S206. Steps S208 of the ACM algorithm of the present invention are followed if it is not possible to successfully use those alternative algorithms of step S204 to determine ALOC and set the new prevailing A-PACE energy as determined in step S206.
These steps S202–S206 (and corresponding steps S302–S306 of
For example, under certain conditions, A-PACE and V-PACE pulses may be repetitively delivered in steps S108 and S114, respectively, of
In each of the ACM algorithms of the present invention, steps S210–S228, S310–S328, and S410–S428 are repeated a number of times to determine one or both of the test A-PACE pulse width and pulse amplitude at ALOC. When both A-PACE pulse width and pulse amplitude at ALOC are determined the test A-PACE pulse energy is automatically incremented or decremented depending on where the ACM algorithm is in its total cycle. Since it is necessary to perform the rheobase test first, the pacing pulse amplitude is decremented at a given test A-PACE pulse width. For example, the test A-PACE pulse width can be set at 0.4 ms, and the A-PACE pulse amplitude can be decreased incrementally at this pulse width, and the steps repeated, until ALOC occurs. Then, the test A-PACE pulse amplitude can be increased incrementally, and the steps repeated until A-CAPTURE is regained. The test A-PACE pulse amplitude at which capture is regained (the “rheobase” threshold) is used as a benchmark A-PACE pulse amplitude to use during the chronaxie test for ALOC and recapture. The test A-PACE pulse amplitude is doubled from the rheobase while the test A-PACE pulse width is decremented to lose capture and incremented to regain A-CAPTURE. Thus, the pulse width is decreased from a known value until LOC occurs, and then increased until capture is again attained to determine the “chronaxie” threshold.
However, it is sufficient to determine only one of the test A-PACE pulse width or pulse amplitude at ALOC and to use that test A-PACE pulse width or pulse amplitude to set the A-PACE pulse energy. Therefore, the depicted steps S208–S226 show the determination of only one of the test A-PACE pulse width or pulse amplitude at ALOC. Generally, the determination of a test A-PACE pulse width or pulse amplitude at ALOC is repeated a number of times, e.g., 2 out of 3 successive times, to increase assurance that it has been accurately determined.
The ACM algorithms of the present invention allow a slow intrinsic atrial heart rate that occurs when delivered test A-PACE pulses result in ALOC to be detected. The slow intrinsic atrial heart rate is normally suppressed by delivered A-PACE pulses resulting in A-CAPTURE. ALOC is declared if an A-EVENT of the slow intrinsic atrial heart rate is detected either during an ACM test window timed from the last delivered test A-PACE pulse or during delivery of a sequence of test A-PACE pulses delivered within or defining the ACM test window.
Steps S208, S308, and S408 of the ACM algorithms of
In the first ACM algorithm of
In general terms, ALOC is declared if a refractory AR-EVENT or non-refractory A-EVENT (collectively designated “AS” in the figures) occurs during the delivery of the TAP pulses as determined in step S214 that is not due to a retrograde conducted ventricular depolarization due to sensing of the far field R-wave as determined in step S216. Such an AS occurring toward the end of the ACM test window satisfying step S214 is shown in
The abort count is incremented in step S218 if the AS is determined to be due to retrograde conduction or far field sensing of ventricular depolarizations in step S216. Steps S208–S216 are repeated employing the same test A-PACE PW and PA if the abort count does not match or exceed a threshold as determined in step S220. The abort count is again incremented in step S218 if the AS is determined to be due to retrograde conduction or far field sensing of ventricular depolarizations in step S216. The ACM is halted and normal pacing is resumed in step S200 if the abort count does match or exceed a threshold as determined in step S220. The abort count can also be incremented for a variety of reasons including those described in the above-referenced U.S. patent application Ser. Nos. 10/004,164 and 10/434,689.
Preferably, a provisional declaration of ALOC (ALOC*) is declared in step S222 if an AS occurs during the delivery of the TAP pulses as determined in step S214 that is not due to a retrograde conducted ventricular depolarization due to sensing of the far field R-wave as determined in step S216. A final ALOC declaration is made when the AS of the slow intrinsic atrial heart rate is detected within the ACM test window in repeated delivery of the test A-PACE pulses and time-out of the ACM test window. Therefore, the TAP PW or PA data is also temporarily stored in step S222 when step S214 is satisfied and step S216 is not satisfied. The new prevailing P-PACE PW and PA are formulated in step S226 when ALOC* is declared in 2 out of 3 (for example) repetitions of steps S208–S222 at the same TAP PW or PA as determined and controlled in step S224.
If both the TAP PW at ALOC and TAP PA at ALOC are to be determined, then the ACM algorithm steps S208–S224 are repeated following the above-described sequence to determine the rheobase and chronaxie ALOC data that are used in step S226 to formulate the prevailing A-PACE PW and PA employed in step S200 until the next time that the ACM algorithm is invoked following steps S202–S206.
In the second ACM algorithm depicted in
The post-ventricular and post-atrial blanking and refractory periods continue to be timed out as described above with respect to
In the third ACM algorithm depicted in
An example of a retrograde conduction of or far field sensing of a ventricular R-wave applicable to all the ACM algorithms is also illustrated in
All patents and publications referenced herein are hereby incorporated by reference in their entireties.
It will be understood that certain of the above-described structures, functions and operations of the above-described preferred embodiments are not necessary to practice the present invention and are included in the description simply for completeness of an exemplary embodiment or embodiments. In addition, it will be understood that specifically described structures, functions and operations set forth in the above-referenced patents can be practiced in conjunction with the present invention, but they are not essential to its practice. It is therefore to be understood, that within the scope of the appended claims, the invention may be practiced otherwise than as specifically described without actually departing from the spirit and scope of the present invention.
|Cited Patent||Filing date||Publication date||Applicant||Title|
|US3920024||Apr 16, 1973||Nov 18, 1975||Vitatron Medical Bv||Threshold tracking system and method for stimulating a physiological system|
|US4428378||Nov 19, 1981||Jan 31, 1984||Medtronic, Inc.||Rate adaptive pacer|
|US4686988||Oct 19, 1984||Aug 18, 1987||Sholder Jason A||Pacemaker system and method for measuring and monitoring cardiac activity and for determining and maintaining capture|
|US4890617||Nov 25, 1987||Jan 2, 1990||Medtronic, Inc.||Dual chamber activity responsive pacer|
|US5144949||Mar 15, 1991||Sep 8, 1992||Medtronic, Inc.||Dual chamber rate responsive pacemaker with automatic mode switching|
|US5165404||Apr 12, 1991||Nov 24, 1992||Siemens Aktiengesellschaft||Biological tissue stimulation device with control means for determining stimulation sensitivity calculation timing|
|US5165405||Jul 8, 1991||Nov 24, 1992||Siemens Aktiengesellschaft||Apparatus for tissue stimulation|
|US5172690||Oct 26, 1990||Dec 22, 1992||Telectronics Pacing Systems, Inc.||Automatic stimulus artifact reduction for accurate analysis of the heart's stimulated response|
|US5222493||Oct 1, 1990||Jun 29, 1993||Siemens Pacesetter, Inc.||Verification of capture using an indifferent electrode mounted on the pacemaker connector top|
|US5285780||Nov 26, 1991||Feb 15, 1994||Nippon Zeon Co., Ltd.||Pacemaker with improved pulse detection|
|US5320643||Oct 6, 1992||Jun 14, 1994||Medtronic, Inc.||Automatic cardiac capture restoration and threshold-seeking method and apparatus|
|US5324310||Jul 1, 1992||Jun 28, 1994||Medtronic, Inc.||Cardiac pacemaker with auto-capture function|
|US5331966||Dec 16, 1993||Jul 26, 1994||Medtronic, Inc.||Subcutaneous multi-electrode sensing system, method and pacer|
|US5476486||Mar 4, 1994||Dec 19, 1995||Telectronics Pacing Systems, Inc.||Automatic atrial pacing pulse threshold determination utilizing an external programmer and a V-sense electrode|
|US5476487||Dec 28, 1994||Dec 19, 1995||Pacesetter, Inc.||Autothreshold assessment in an implantable pacemaker|
|US5564430||Nov 16, 1994||Oct 15, 1996||Ela Medical S.A.||Automatic control of the sensing threshold for monitoring cardiac rhythm in a implantable device|
|US5601615||Aug 16, 1994||Feb 11, 1997||Medtronic, Inc.||Atrial and ventricular capture detection and threshold-seeking pacemaker|
|US5626623||Apr 30, 1996||May 6, 1997||Medtronic, Inc.||Method and apparatus for optimizing pacemaker AV delay|
|US5674254||May 22, 1995||Oct 7, 1997||Vitatron Medical, B.V.||Cardiac pacemaker system and method for determining a measure of pacing threshold without incurring loss of capture|
|US5683426||Aug 29, 1996||Nov 4, 1997||Pacesetter, Inc.||Apparatus and method for detecting the progression of AV nodal block and atrial capture|
|US5683431||Mar 27, 1996||Nov 4, 1997||Medtronic, Inc.||Verification of capture by sensing evoked response across cardioversion electrodes|
|US5861012||Oct 18, 1996||Jan 19, 1999||Medtronic, Inc.||Atrial and ventricular capture detection and threshold-seeking pacemaker|
|US5861013||Apr 29, 1997||Jan 19, 1999||Medtronic Inc.||Peak tracking capture detection circuit and method|
|US5902324||Apr 28, 1998||May 11, 1999||Medtronic, Inc.||Bi-atrial and/or bi-ventricular sequential cardiac pacing systems|
|US6134473||Apr 14, 1999||Oct 17, 2000||Medtronic, Inc.||Microprocessor capture detection circuit and method|
|US6144881||Sep 18, 1998||Nov 7, 2000||Medtronic, Inc.||Capture detection circuit for pulses and physiologic signals|
|US6216037||Jan 29, 1999||Apr 10, 2001||Medtronic Inc,||Pacemaker system with simplified atrial capture detection based on QT interval|
|US6311088||Apr 13, 1999||Oct 30, 2001||Medtronic, Inc.||Dual-chamber pacemaker with optimized PVARP following event that may disrupt AV synchrony|
|US6389316 *||Jan 11, 2000||May 14, 2002||Pacesetter, Inc.||System and method for automatic atrial capture detection and atrial pacing threshold determination|
|US6584354||Jul 17, 2001||Jun 24, 2003||Pacesetter, Inc.||Implantable stimulation device and method for determining atrial autocapture using PVC response|
|US6587723||Oct 17, 2000||Jul 1, 2003||Pacesetter, Inc.||Method and system for automatically measuring capture threshold in an implantable cardiac stimulation device|
|EP0850662A2||Jul 31, 1995||Jul 1, 1998||Medtronic, Inc.||Atrial and ventricular capture detection and threshold-seeking pacemaker|
|EP1155712A2||May 15, 2001||Nov 21, 2001||Pacesetter, Inc.||Implantable dual site cardiac stimulation device having independent automatic capture capability|
|Citing Patent||Filing date||Publication date||Applicant||Title|
|US7587240||Dec 15, 2004||Sep 8, 2009||Cardiac Pacemakers, Inc.||Atrial capture verification|
|US7801610||Nov 17, 2006||Sep 21, 2010||Cardiac Pacemakers, Inc.||Methods and systems for management of atrial retrograde conduction and pacemaker mediated tachyarrhythmia|
|US7908006||Dec 15, 2004||Mar 15, 2011||Cardiac Pacemakers, Inc.||Cardiac pacing response classification using an adaptable classification interval|
|US7930029||Dec 15, 2004||Apr 19, 2011||Cardiac Pacemakers, Inc.||Template initialization for evoked response detection|
|US7957803||Aug 13, 2009||Jun 7, 2011||Cardiac Pacemakers, Inc.||Atrial capture verification|
|US8155741||Nov 21, 2008||Apr 10, 2012||Cardiac Pacemakers, Inc.||Retrograde atrial sensing for identifying sub-threshold atrial pacing|
|US8229561||Dec 15, 2004||Jul 24, 2012||Cardiac Pacemakers, Inc.||Atrial retrograde management|
|US8290590||Nov 17, 2006||Oct 16, 2012||Cardiac Pacemakers, Inc.||Dynamic morphology based atrial automatic threshold|
|US8452405||May 3, 2010||May 28, 2013||Cardiac Pacemakers, Inc.||Methods and systems for mitigating the occurrence of arrhythmia during atrial pacing|
|US8880172||Mar 16, 2012||Nov 4, 2014||Cardiac Pacemakers, Inc.||Retrograde atrial sensing for identifying sub-threshold atrial pacing|
|US8965500||Jul 7, 2014||Feb 24, 2015||Zoll Medical Corporation||Wearable defibrillator with audio input/output|
|US8983597||May 31, 2013||Mar 17, 2015||Zoll Medical Corporation||Medical monitoring and treatment device with external pacing|
|US9204813||Aug 4, 2014||Dec 8, 2015||Zoll Medical Corporation||Method of detecting signal clipping in a wearable ambulatory medical device|
|US9216292||May 3, 2013||Dec 22, 2015||Cardiac Pacemakers, Inc.||Dynamic morphology based atrial automatic threshold|
|US9227073||Sep 12, 2012||Jan 5, 2016||Cardiac Pacemakers, Inc.||Dynamic morphology based atrial automatic threshold|
|US9308376||Apr 9, 2014||Apr 12, 2016||Medtronic, Inc.||Method and apparatus for detecting loss of capture|
|US9320904||Jan 30, 2015||Apr 26, 2016||Zoll Medical Corporation||Medical monitoring and treatment device with external pacing|
|US9408548||Nov 7, 2014||Aug 9, 2016||Zoll Medical Corporation||Selection of optimal channel for rate determination|
|US9452292||Apr 25, 2014||Sep 27, 2016||Medtronic, Inc.||Method and apparatus for detecting loss of capture|
|US9456778||Nov 3, 2015||Oct 4, 2016||Zoll Medical Corporation||Method of detecting signal clipping in a wearable ambulatory medical device|
|US9492676||Jan 28, 2015||Nov 15, 2016||Zoll Medical Corporation||Wearable defibrillator with audio input/output|
|US9675804||Mar 24, 2016||Jun 13, 2017||Zoll Medical Corporation||Medical monitoring and treatment device with external pacing|
|US20060129194 *||Dec 15, 2004||Jun 15, 2006||Geng Zhang||Cardiac pacing response classification using an adaptable classification interval|
|US20060129199 *||Dec 15, 2004||Jun 15, 2006||Geng Zhang||Atrial retrograde management|
|US20080119902 *||Nov 17, 2006||May 22, 2008||Bohn Derek D||Methods and systems for management of atrial retrograde conduction and pacemaker mediated tachyarrhythmia threshold|
|US20080119905 *||Nov 17, 2006||May 22, 2008||Bohn Derek D||Dynamic morphology based atrial automatic threshold|
|US20090076564 *||Nov 21, 2008||Mar 19, 2009||Bohn Derek D||Retrograde Atrial Sensing for Identifying Sub-Threshold Atrial Pacing|
|US20090306737 *||Aug 13, 2009||Dec 10, 2009||Geng Zhang||Atrial Capture Verification|
|US20100286743 *||May 3, 2010||Nov 11, 2010||Enrooth Eric K||Methods and Systems for Mitigating the Occurrence of Arrhythmia During Atrial Pacing|
|WO2013181617A3 *||May 31, 2013||Apr 9, 2015||Zoll Medical Corporation||Medical monitoring and treatment device with external pacing|
|U.S. Classification||607/28, 607/25, 607/27, 607/9|
|International Classification||A61N1/362, A61N1/37|
|Cooperative Classification||A61N1/3712, A61N1/362, A61N1/3714|
|European Classification||A61N1/37D2, A61N1/362|
|Jul 23, 2003||AS||Assignment|
Owner name: MEDTRONIC, INC., MINNESOTA
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:RUETER, JOHN C.;SHELDON, TODD J.;REEL/FRAME:014328/0638;SIGNING DATES FROM 20030722 TO 20030723
|Mar 23, 2010||FPAY||Fee payment|
Year of fee payment: 4
|Apr 30, 2014||FPAY||Fee payment|
Year of fee payment: 8